Imaging apparatus, imaging method, and storage medium

ABSTRACT

The object of this invention is to provide an imaging apparatus capable of providing a high-quality image optimum for medical diagnosis or the like by an arrangement for preventing any degradation in image quality due to the influence of electromagnetic noise and vibration caused by grid movement. In order to achieve this object, as operation control in receiving radiation transmitted through an object by an image sensing element through a movable grid and reading the accumulated signal from the image sensing element, a control device stops moving drive movement of the grid after the end of radiation irradiation for the object, and after the stop of moving drive stopping the movement, starts reading the accumulated signal from the image sensing element.

Notice: More than one reissue application has been filed for the reissueof U.S. Pat. No. 6,510,202. The reissue applications are applicationSer. No. 11/039,456 (the present application) and application Ser. No.11/039,457, all of which are divisional reissues of U.S. Pat. No.6,510,202.

FIELD OF THE INVENTION

The present invention relates to an imaging apparatus, imaging method,and computer-readable storage medium which stores processing steps inexecuting the method, which are used for, e.g., an apparatus or systemfor performing radiation imaging of an object using a grid.

BACKGROUND OF THE INVENTION

Conventionally, a radiation method of irradiating an object withradiation such as X-rays and detecting the intensity distribution of theradiation transmitted through the object to acquire the radiation imageof the object is widely used in the field of industrial non-destructiveinspection or medical diagnosis.

In the most popular radiation imaging method, a combination of aso-called “screen” which emits fluorescent light by radiation and asilver halide film is used.

In the above radiation imaging method, first, an object is irradiatedwith radiation. The radiation transmitted through the object isconverted into visible light by the screen to form a latent image on thesilver halide film. After that, the silver halide film is chemicallyprocessed to acquire a visible image.

A thus obtained film image (radiation image) is a so-called analogpicture and is used for medical diagnosis or inspection.

A computed radiography apparatus (to be referred to as a “CR apparatus”hereinafter) which acquires a radiation image using an imaging plate (tobe referred to as an “IP” hereinafter) coated with a stimulable phosphoras a phosphor is also being put into practice.

When an IP primarily excited by radiation irradiation is secondarilyexcited by visible light such as a red laser beam, light calledstimulable fluorescent light is emitted. The CR apparatus detects thislight emission using a photosensor such as a photomultiplier to acquirea radiation image and outputs a visible image to a photosensitivematerial or CRT on the basis of the radiation image data.

Although the CR apparatus is a digital imaging apparatus, it is regardedas an indirect digital imaging apparatus because the image formationprocess, reading by secondary excitation, is necessary.

The reason for “indirect” is that the apparatus cannot instantaneouslydisplay the radiation image, like the above-described apparatus (to bereferred to as an “analog imaging apparatus” hereinafter) which acquiresan analog radiation image such as an analog picture.

In recent years, a technique has been developed, which acquires adigital radiation image using a photoelectric conversion device in whichpixels formed from small photoelectric conversion elements or switchingelements are arrayed in a matrix as an image detection means foracquiring a radiation image from radiation through an object.

Examples of a radiation imaging apparatus employing the above technique,i.e., having phosphors stacked on a sensor such as a CCD or amorphoussilicon two-dimensional image sensing element are disclosed in U.S. Pat.Nos. 5,418,377, 5,396,072, 5,381,014, 5,132,539, and 4,810,881.

Such a radiation imaging apparatus can instantaneously display acquiredradiation image data and is therefore regarded as a direct digitalimaging apparatus.

As advantages of the indirect or direct digital imaging apparatus overthe analog imaging apparatus, a filmless system, an increase in acquiredinformation by image processing, and database construction becomepossible.

An advantage of the direct digital imaging apparatus over the indirectdigital imaging apparatus is instantaneity. The direct digital imagingapparatus can be effectively used on, e.g., a medical scene with urgentneed because a radiation image obtained by imaging can be immediatelydisplayed at that place.

When the radiation imaging apparatus described above is used as amedical apparatus to detect the radiation transmission distribution of apatient as an object to be examined, a scattering ray removing membercalled a “grid” is normally inserted between the patient and a radiationtransmission distribution detector (to be also simply referred to as a“detector” hereinafter) to reduce the influence of scattering raysgenerated when radiation is transmitted through the person to beexamined.

A grid is formed by alternately arranging a thin foil of a material suchas lead which hardly passes radiation and that of a material such asaluminum which readily passes radiation perpendicularly to theirradiation direction of radiation.

With this structure, radiation components such as scattering rays in thepatient, which are generated when the patient is irradiated withradiation and have angles with respect to the axis of irradiation, areabsorbed by the lead foil in the grid before they reach the detector.For this reason, a high-contrast image can be obtained.

If the grid stands still during imaging, the radiation reaching the leadin the grid is wholly absorbed including both the scattering rays andthe primary rays of radiation. Since a distribution differencedistribution corresponding to the array in the grid is formed at thedetection section, a striped radiation image is detected, resulting ininconvenience in reading at the time of image diagnosis or the like.

A radiation imaging apparatus having a mechanism for moving the gridduring imaging has already been placed on the market.

However, in the above-described conventional radiation imaging apparatushaving a grid, a light receiving scheme using a sensor such as a CCD oramorphous silicon two-dimensional image sensing element is not used, anda signal read by a two-dimensional solid-state image sensing element isreal-time electrical processing. For this reason, unlike an analogimaging apparatus or an indirect digital imaging apparatus such as a CRapparatus, the influence of vibration of the imaging section or theelectromagnetic influence of the driving motor due to grid movementposes a problem.

More specifically, the vibration of the imaging section due to gridmovement also vibrates the capacitor and signal lines. The weak electriccapacitance varies, and noise is superposed on the radiation image.

Additionally, in the signal read by the sensor, when the motor is drivennear the sensor to move the grid, the signal potential or control powersupply potential varies due to the influence of electromagnetic noise,and noise is superposed on the radiation image.

The radiation image with noise superposed thereon may deteriorate, e.g.,the medical diagnostic performance.

On the other hand, in the sensor such as a two-dimensional solid-stateimage sensing element, the amount of charges accumulated in the sensorincreases in proportion to the signal accumulation time due to theinfluence of a dark current even in an unexposed state. The larger theamount of charges that do not contribute to an image signal becomes, thelarger the noise added to the output image signal becomes.

Hence, imaging control is preferably optimized to make the accumulationtime in the sensor as short as possible while eliminating the influenceof grid vibration. Neither an apparatus nor system that implement suchcontrol are conventionally available.

In the conventional X-ray imaging apparatus, an X-ray beam is projectedfrom an X-ray source through an object such as a medical patient to beanalyzed. After the X-ray beam passes through the object to be examined,normally, an image intensifier converts the X-ray radiation into avisible light image, a video camera generates an analog video signalfrom the visible image, and the video signal is displayed on a monitor.Since an analog video signal is generated, image processing forautomatic luminance adjustment and image enhancement is performed in ananalog domain.

A solid-state X-ray detector having high resolving power has alreadybeen proposed, which is constructed by a two-dimensional array using3,000 to 4,000 detection elements represented by photodiodes for eachdimension. Each element generates an electrical signal corresponding toa pixel luminance of an X-ray image projected to the detector. Thesignals from the respective elements are individually read anddigitized. Then, the signals are subjected to image processing, stored,and displayed.

A medical X-ray image need needs to have 4,096 or more grayscale levels.In addition, since the X-ray dose is preferably suppressed to reduce theexposure amount, the image signal amount is also limited. For thisreason, an extremely noise-free system is required as compared to ageneral image sensing element.

In medical X-ray imaging, a grid is used to suppress the influence ofX-ray scattering. A fixed grid is generally unsuitable to with asolid-state X-ray image sensing element and poses a problem of aliasing,a system may be built using a movable grid.

As described above, a medical X-ray image sensing apparatus is requiredto be noise-free. A vibration caused by the movable grid can be a newnoise source. The noise is generated by, e.g., the piezoelectric effectof a high-permittivity capacitor used in a circuit for generating areference potential or simply because the parasitic capacitance in theread circuit varies due to the vibration.

To obtain the highest image quality, grid drive control, X-ray detectormovement control, and X-ray detector driving method must beappropriately executed.

SUMMARY OF THE INVENTION

The present invention has been made to solve the above problem, and hasas its object to provide an imaging apparatus, imaging method, andcomputer-readable storage medium which stores processing steps ofexecuting the method, which can provide a high-quality image optimum formedical diagnosis or the like by an arrangement for preventing anydegradation in image quality due to the influence of electromagneticnoise and vibration caused by grid movement.

It is another object of the present invention to provide an imagingapparatus and method which can easily and reliably obtain a satisfactoryimage without any influence of vibration of a grid or X-ray detectionmeans system by a very simple arrangement.

In order to achieve the above objects, an imaging apparatus according tothe first aspect of the present invention is characterized by thefollowing arrangement.

That is, there is provided an imaging apparatus which has a movableelement related to imaging and an image sensing element, and has afunction of sensing an image of an object with the image sensing elementand reading as an image signal a signal generated by the image sensingelement, comprising control means system for stopping moving movement ofthe element related to imaging, and after the stop of stopping themovement, starting reading the of a signal generated by the imagesensing element.

An imaging apparatus according to the second aspect of the presentinvention is characterized by the following arrangement.

That is, there is provided an imaging apparatus which has a movableelement related to imaging and an image sensing element, and has afunction of sensing an image of an object with the image sensing elementand reading as an image signal a signal generated by the image sensingelement, comprising drive means system for moving the element related toimaging by the image sensing element, and control means system forcontrolling to cause the drive means system to operate the elementrelated to imaging at a predetermined speed without any accelerationduring an operation period related to a read reading a signal from theimage sensing element.

An imaging apparatus according to the third aspect of the presentinvention is characterized by the following arrangement.

That is, there is provided an imaging apparatus which has a movableelement related to imaging and an image sensing element, and has afunction of sensing an image of an object with the image sensing elementand reading as an image signal a signal generated by the image sensingelement, comprising drive means system for moving the element related toimaging by the image sensing element, and control means system forcontrolling to cause the drive means system to operate the elementrelated to imaging at a uniform acceleration during an operation periodrelated to a read reading a signal from the image sensing element.

An imaging apparatus according to the fourth aspect of the presentinvention is characterized by the following arrangement.

That is, there is provided an imaging apparatus which has a movableelement related to imaging and an image sensing element, and has afunction of sensing an image of an object with the image sensing elementand reading as an image signal a signal generated by the image sensingelement, comprising drive means system for moving the element related toimaging by the image sensing element, and control means system forcontrolling to execute execution of a drive operation related to imageacquisition upon determining that a value of a vibration is not morethan a predetermined value during an operation period related to animage read from the image sensing element.

An imaging apparatus according to the fifth aspect of the presentinvention is characterized by the following arrangement.

That is, there is provided an imaging apparatus having a function ofsensing an image of an object with an image sensing element and readingas an image signal a signal generated by the image sensing element,comprising drive means system for moving the image sensing element, andcontrol means system for stopping moving movement of the image sensingelement by the drive means system, and after the stop of stopping themovement, starting reading of an accumulated signal from the imagesensing element.

An imaging apparatus according to the sixth aspect of the presentinvention is characterized by the following arrangement.

That is, there is provided an imaging apparatus having a function ofsensing an image of an object with an image sensing element and readingas an image signal a signal generated by the image sensing element,comprising drive means system for moving the image sensing element, andcontrol means system for controlling to cause the drive means system tooperate the image sensing element at a predetermined speed without anyacceleration during an operation period related to a read reading of asignal from the image sensing element.

An imaging apparatus according to the seventh aspect of the presentinvention is characterized by the following arrangement.

That is, there is provided an imaging apparatus having a function ofsensing an image of an object with an image sensing element and readingas an image signal a signal generated by the image sensing element,comprising drive means system for moving the image sensing element, andcontrol means system for controlling to cause the drive means system tooperate the image sensing element at a uniform acceleration during anoperation period related to a read reading a signal from the imagesensing element.

An imaging apparatus according to the eighth aspect of the presentinvention is characterized by the following arrangement.

That is, there is provided an imaging apparatus having a function ofsensing an image of an object with an image sensing element and readingas an image signal a signal generated by the image sensing element,comprising drive means system for moving the image sensing element, andcontrol means system for controlling to execute execution of a driveoperation related to image acquisition upon determining that a value ofa vibration is not more than a predetermined value during an operationperiod related to an image read from the image sensing element.

An imaging method according to the first aspect of the present inventionis characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with an image sensing element and reading a signal generated bythe image sensing element while moving a movable element related toimaging, comprising the step of stopping moving movement of the elementrelated to imaging, and after the stop of stopping the movement,starting reading the signal from the image sensing element.

An imaging method according to the second aspect of the presentinvention is characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with an image sensing element and reading a signal generated bythe image sensing element while moving a movable element related toimaging, comprising the step of, in moving the element related toimaging at the time of image sensing by the image sensing element,controlling to operate operation of the element related to imaging at apredetermined speed without any acceleration during an operation periodrelated to a read of the reading a signal from the image sensingelement.

An imaging method according to the third aspect of the present inventionis characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with an image sensing element and reading a signal generated bythe image sensing element while moving a movable element related toimaging, comprising the step of, in moving the element related toimaging at the time of image sensing by the image sensing element,controlling to operate operation of the element related to imaging at auniform acceleration during an operation period related to a read of thereading a signal from the image sensing element.

An imaging method according to the fourth aspect of the presentinvention is characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with an image sensing element and reading a signal generated bythe image sensing element while moving a movable element related toimaging, comprising the step of, in moving the element related toimaging at the time of image sensing by the image sensing element,controlling to execute execution of a drive operation related to imageacquisition upon determining that a value of a vibration of the imagesensing element is not more than a predetermined value during anoperation period related to an image read from the image sensingelement.

An imaging method according to the fifth aspect of the present inventionis characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with a movable image sensing element and reading a signalgenerated by the image sensing element, comprising the step of stoppingmoving movement of the image sensing element, and after the stop ofstopping the movement, starting reading the of a signal from the imagesensing element.

An imaging method according to the sixth aspect of the present inventionis characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with a movable image sensing element and reading a signalgenerated by the image sensing element, comprising the step ofcontrolling to operate operation of the image sensing element at apredetermined speed without any acceleration during an operation periodrelated to a read of the reading a signal from the image sensingelement.

An imaging method according to the seventh aspect of the presentinvention is characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with a movable image sensing element and reading a signalgenerated by the image sensing element, comprising the step ofcontrolling to operate operation of the image sensing element at auniform acceleration during an operation period related to a read of thereading a signal from the image sensing element.

An imaging method according to the eighth aspect of the presentinvention is characterized by the following step.

That is, there is provided an imaging method of sensing an image of anobject with a movable image sensing element and reading a signalgenerated by the image sensing element, comprising the step ofcontrolling to execute execution of a drive operation related to imageacquisition upon determining that a value of a vibration of the imagesensing element is not more than a predetermined value during anoperation period related to an image read from the image sensingelement.

A computer-readable storage medium according to the present invention ischaracterized in that the storage medium stores a processing program forexecuting the above imaging method.

Other objects and advantages besides those discussed above shall beapparent to those skilled in the art for the description of a preferredembodiment of the invention which follows. In the description, referenceis made to accompanying drawings, which form a part hereof, and whichillustrate an example of the invention. Such example, however, is notexhaustive of the various embodiments of the invention, and thereforereference is made to the claims which follow the description fordetermining the scope of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a block diagram showing the arrangement of a radiation imagingsystem according to the first embodiment, to which the present inventionis applied;

FIG. 2 is a flow chart for explaining operation of the radiation imagingsystem;

FIGS. 3A to 3F are timing charts for explaining the operation controltiming of the radiation imaging system;

FIG. 4 is a block diagram showing the arrangement of a radiation imagingsystem according to the second embodiment, to which the presentinvention is applied;

FIG. 5 is a flow chart for explaining operation of the radiation imagingsystem;

FIGS. 6A to 6H are timing charts for explaining the operation controltiming of the radiation imaging system;

FIG. 7 is a view showing the schematic arrangement of an X-ray imagesensing system;

FIG. 8 is a circuit diagram showing an equivalent circuit of a firstphotodetection section;

FIGS. 9A to 9C are views showing the energy band of the firstphotodetection section;

FIG. 10 is a circuit diagram showing an equivalent circuit of a secondphotodetection section;

FIG. 11 is a schematic view showing the arrangement of a photodetectorarray;

FIG. 12 is a timing chart showing the driving concept of thephotodetector array;

FIG. 13 is a timing chart of an X-ray image sensing system according tothe third embodiment;

FIG. 14 is a flow block diagram showing processing for an acquiredimage;

FIG. 15 is a schematic view showing the structure of a first movablegrid;

FIG. 16 is a schematic view showing the structure of a second movablegrid;

FIG. 17 is a view showing the schematic arrangement of an X-ray imagesensing system according to the fourth embodiment;

FIG. 18 is a timing chart of an X-ray image sensing system according tothe fourth embodiment; and

FIG. 19 is a timing chart of an X-ray image sensing system according tothe fifth embodiment.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The embodiments of the present invention will be described below withreference to the accompanying drawings.

(First Embodiment)

The present invention is applied to, e.g., a radiation imaging system100 as shown in FIG. 1.

<Arrangement of Radiation Imaging System 100>

As shown in FIG. 1, the radiation imaging system 100 has an arrangementin which an imaging device 110 for acquiring an image signal of anobject (patient) 102 to be examined, a control device 111 forcontrolling the entire system 100, a storage device 112 for storingvarious data such as a control program for control processing by thecontrol device 111 and the image, a display device 113 for displayingthe image or the like, an image processing device 114 for executingarbitrary image processing for the image signal of the patient 102,which is obtained by the imaging device 110, an imaging conditioninstruction device 115 for instructing various imaging conditions in theimaging device 110, an imaging button 116 for instructing the system 100to start imaging operation, and a radiation generator 117 for generatinga radiation (e.g., X-rays) from a radiation tube 101 to the patient 102are connected to each other through a system bus 120 to exchange data.

The imaging device 110 is located at a position where the radiationgenerated from the radiation tube 101 of the radiation generator 117 canbe received through the patient 102, and comprises a chest stand 103,grid 104, phosphor 105, sensor (two-dimensional solid-state imagesensing element) 106, signal reading section 107, and grid movingsection 108.

The chest stand 103, grid 104, phosphor 105, and sensor 106 are arrangedin this order from the side of the radiation tube 101 of the radiationgenerator 117.

<Series of Operations of Radiation Imaging System 100>

Outlines of the imaging procedure and radiation image generation processin the radiation imaging system 100 will be described here.

The user (e.g., radiation technician) positions the patient 102 to thechest stand 103 and selectively inputs appropriate imaging conditions(e.g., tube voltage, tube current, irradiation time, type of sensor 106,and type of radiation tube 101) using the imaging condition instructiondevice 115.

In this embodiment, the imaging conditions are manually input by theuser through the imaging condition instruction device 115. However, thepresent invention is not limited to this. For example, the imagingconditions may be input through a network (not shown) connected to theimaging device 110.

Next, the user presses the imaging button 116 to request the controldevice 111 to start imaging operation.

After receiving the imaging operation start request from the user, thecontrol device 111 performs initialization necessary in the system 100and prompts the radiation generator 117 to irradiate the person withradiation.

In accordance with the irradiation instruction from the control device111, the radiation generator 117 generates radiation from the radiationtube 101.

The radiation generated from the radiation tube 101 passes through thepatient 102 and reaches chest stand 103.

The chest stand 103 is exposed by the radiation transmitted through thepatient 102 with a transmitted radiation distribution in accordance withthe structure in the patient 102.

Since the chest stand 103 is sufficiently transparent to the radiation,the radiation transmitted through the chest stand 103 reaches the grid104.

The grid 104 removes scattering ray components in the radiationtransmitted through the chest stand 103 and sends only effectiveradiation components to the phosphor 105.

The phosphor 105 converts the radiation (effective radiation) from thegrid 104 into visible light in accordance with the spectral sensitivityof the sensor 106.

The sensor 106 receives the radiation from the phosphor 105, convertsthe radiation light into an electrical signal (image signal) bytwo-dimensional photoelectric conversion, and accumulates it.

The present invention is not limited to this. The sensor 106 maydirectly convert the radiation from the grid 104 to the electricalsignal (image signal).

The signal reading section 107 reads the image signal accumulated in thesensor 106 and stores the signal in the storage device 112 as aradiation image signal.

The image processing device 114 performs appropriate image processingfor the radiation image signal stored in the storage device 112.

The display device 113 displays the radiation image signal afterprocessing by the image processing device 114.

<Most Characteristic Operation and Arrangement of Radiation ImagingSystem 100>

FIG. 2 is a flow chart showing operation control processing executed bythe control device 111 for the system 100. FIGS. 3A to 3F are timingcharts showing the operation control timing.

The processing shown in FIG. 2 corresponds to processing from theabove-described imaging condition input by the user to image signal readfrom the sensor 106.

Step S201

The control device 111 recognizes an irradiation time T exp, the type ofsensor 106 used for imaging, and the type of radiation tube 101 on thebasis of imaging conditions selectively input by the user through theimaging condition instruction device 115.

In accordance with the recognized information, the control device 111determines control until radiation irradiation and control afterradiation irradiation by processing from step S202.

Step S202

The control device 111 determines a sensor initialization time Tss inaccordance with the type of sensor 106.

The sensor initialization time Tss changes depending on the type ofsensor 106. For example, when the sensor 106 requires predischarge of adark current, the pre-read time is the sensor initialization time Tss.From this time, signal accumulation in the sensor 106 starts.

Step S203

The control device 111 determines a grid initialization time Tgs andgrid vibration convergence time Tge from the irradiation time T exp.

More specifically, to reduce stripe image formation on the object by thegrid 104, for example, radiation must be transmitted through stripes of10 or more cycles. However, the moving distance of the grid 104 islimited. Hence, the moving speed of the grid 104 must be optimized inaccordance with the irradiation time T exp. In addition, since the grid104 generally has a focal point, the irradiation central position ofradiation and the central position of the grid 104 must be aligned toobtain an image with a satisfactory quality.

Hence, a time required until the optimum moving speed (target movingspeed) of the grid 104 is obtained and the position of the grid 104reaches the irradiation central position (target position) of radiationcorresponds to the grid initialization time Tgs.

In this embodiment, the grid initialization times Tgs until the targetmoving speed and position of the grid 104 are obtained and the gridvibration convergence times Tge required to converge device vibrationcaused by movement are obtained as a table by experiments incorrespondence with, e.g., various patterns of irradiation time T expand moving speed of the grid 104 and stored in the storage device 112 inadvance. The grid initialization time Tgs and grid vibration convergencetime Tge corresponding to the actually obtained irradiation time T expare determined from the table information in the storage device 112.

Step S204

The control device 111 determines a pre-irradiation delay time Txs andpost-irradiation delay time Txe on the basis of the type of radiationtube 101.

The pre-irradiation delay time Txs is a time after the radiationgenerator 117 is instructed to permit radiation irradiation until theradiation generator 117 actually starts radiation irradiation, and isdetermined by the type of radiation generator 117 or radiation tube 101.

In this embodiment, the pre-irradiation delay times Txs correspondingto, e.g., various types of radiation generator 117 or radiation tube 101are prepared as a table in advance, and a corresponding pre-irradiationdelay time Txs is determined from the table information.

The post-irradiation delay time Txe is a delay time after the elapse ofirradiation time T exp until the radiation generator 117 actually endsthe radiation irradiation. The post-irradiation delay time Txe is alsodetermined in accordance with the same procedure as that for thepre-irradiation delay time Txs.

Step S205

The control device 111 determines an irradiation delay time T1.

The irradiation delay time T1 is a delay time after an imaging requestis input by the user through the imaging button 116 until the radiationgenerator 117 actually starts radiation irradiation. Of the sensorinitialization time Tss determined in step S202, the grid initializationtime Tgs determined in step S203, and the pre-irradiation delay time Txsdetermined in step S204, the longest time is determined as theirradiation delay time T1.

Step S206

The control device 111 determines a time table before irradiation.

This time table is determined from the sensor initialization time Tssdetermined in step S202, the grid initialization time Tgs determined instep S203, and the pre-irradiation delay time Txs determined in stepS204.

More specifically, the control sequence and times (timings) ofinitialization of the sensor 106, start of drive of the grid 104, andradiation irradiation instruction (irradiation permission) to theradiation generator 117 after the imaging request input by the userthrough the imaging button 116 is recognized are determined bysubtracting each delay time from the irradiation delay time T1determined in step S205.

The initialization timing of the sensor 106 is determined as “Tl−Tss”.The drive start timing of the grid 104 is determined as “Tl−Tgs”. Theradiation irradiation instruction (irradiation permission) timing forthe radiation generator 117 is determined as “Tl−Txs”.

Step S207

After control before radiation irradiation is control parameters aredetermined in the above-described way, the control device 111 determineswhether an imaging request is input by the user through the imagingbutton 116 and stands by until an imaging request is received.

Step S208

Upon recognizing that an imaging request is input by the user throughthe imaging button 116, the control device 111 executes operationcontrol according to the time table determined in step S206.

Initialization of the sensor 106 is started after the elapse of“Tl−Tss”, drive of the grid 104 is started after the elapse of “Tl−Tgs”,and irradiation permission is executed after the elapse of “TI−Txs”.

Step S209

The control device 111 stands by until the total time (T1+T exp+Txe) ofthe irradiation time (actual exposure time) T exp determined in stepS201, the post-irradiation delay time Txe determined in step S204, andthe irradiation delay time T1 determined in step S205 elapses.

Step S210

When recognizing that the time (T1+T exp+Txe) has elapsed, the controldevice 111 stops driving the grid 104 through the grid moving section108.

Step S211

The control device 111 stands by until the grid vibration convergencetime Tge determined in step S203 elapses.

Step S212

When recognizing that the grid vibration convergence time Tge haselapsed, the control device 111 causes the signal reading section 107 tostart reading the signal accumulated in the sensor 106.

In the operation control for the radiation imaging system 100 shown inthe flow chart of FIG. 2, especially, since the operation stands by forthe post-irradiation delay time Txe after the elapse of irradiation timeT exp, stripe image formation on the object by the grid 104 can beprevented.

In addition, since drive the driving of the grid 104 is stopped, theinfluence of electromagnetic noise generated from the grid movingsection 108 can be prevented.

Furthermore, since the operation stands by for the grid vibrationconvergence time Tge after the stop of drive stopping the driving of thegrid 104, the influence of device vibration can be prevented.

Hence, after the imaging request from the user is recognized, thecontrol device 111 controls the operation of the system 100 inaccordance with the flow chart in FIG. 2, thereby acquiring asatisfactory image.

The above operation control for the radiation imaging system 100 will bedescribed below in more detail with reference to the timing charts shownin FIGS. 3A to 3F.

The timing charts of FIGS. 3A to 3F explain timings after the imagingbutton 116 is pressed.

In accordance with the imaging conditions input by the user, forexample,

-   -   Irradiation time T exp=100 ms    -   Sensor initialization time Tss=200 ms    -   Grid initialization time Tgs=300 ms    -   Pre-irradiation delay time Txs=100 ms    -   Grid vibration convergence time Tge=300 ms    -   Post-irradiation delay time Txe=100 ms are determined.

In this case, the irradiation delay time T1 as the longest time of thesensor initialization time Tss, grid initialization time Tgs, andpre-irradiation delay time Txs is determined byT1=max(Tss, Tgs, Txs)=Tgs=300 ms

Operation control until radiation irradiation is determined from theseinitial conditions.

Next, control timings for sensor initialization, start of grid movement,and irradiation permission instruction after recognition of the imagingrequest are determined by subtracting a corresponding time required foroperation from the irradiation delay time T1.Sensor initialization timing: T1−Tss=100 msGrid movement start timing: T1−Tgs=0 msIrradiation enable signal transmission timing: T1−Txs=200 ms

Control timings after radiation irradiation are so determined thatmovement control for the grid 104 is stopped after the elapse of actualirradiation time obtained by adding the irradiation time T exp andpost-irradiation delay time Txe to the irradiation delay T1, and thesignal read from the sensor 106 is started after the elapse of gridvibration convergence time Tge.

That is, the grid control stop timing and signal read start timing aredetermined byGrid control stop timing: T1+T exp+Txe=500 msSignal read start timing: T1+T exp+Txe+Tge=800 ms

After the control timings are determined, an imaging request (FIG. 3A)input by the user by pressing the imaging button 116 is waited upon.

When an imaging request is recognized, operation control for theradiation imaging system 100 is started on the basis of the determinedcontrol timings.

First, movement (motion) of the grid 104 is started, as shown in FIG.3B.

The moving speed of the grid 104 acceleratingly increases and reaches anirradiation enable state after the elapse of 300 ms (grid initializationtime Tgs=300 ms), as shown in FIG. 3C.

Next, as shown in FIG. 3F, after the elapse of 100 ms (sensorinitialization timing: Tl−Tss=100 ms) from imaging request recognition,initialization of the sensor 106 is started. After the elapse of 200 ms(sensor initialization time Tss=200 ms), initialization of the sensor106 is ended.

As shown in FIG. 3D, after the elapse of 200 ms (irradiation enablesignal transmission timing: Tl−Txs=200 ms) from imaging requestrecognition, the radiation generator 117 is instructed to startirradiation.

The radiation generator 117 starts actual irradiation after the elapseof 100 ms (pre-irradiation delay time Txs=100 ms), as shown in FIG. 3E.

After the elapse of 500 ms (grid control stop timing: T1+T exp+Txe=500ms) from imaging request recognition, actual irradiation by theradiation generator 117 is ended.

At this time, movement control for the grid 104 is stopped, as shown inFIG. 3B, and the moving speed of the grid 104 gradually decreases. Alongwith this deceleration, the vibration of the imaging device 110, that isgenerated by moving the grid 104, starts converging.

After that, as shown in FIG. 3F, after the elapse of 800 ms (signal readstart timing: T1+T exp+Txe+Tge=800 ms) from imaging request recognition,the signal reading section 107 is instructed to end signal accumulationin the sensor 106 and start reading the signal.

At this time, the vibration of the imaging device 110 has become sosmall that it does not affect the image quality. As a result, asatisfactory image can be obtained.

(Second Embodiment)

The present invention is applied to, e.g., a radiation imaging system300 as shown in FIG. 4.

This radiation imaging system 300 has the same arrangement as that ofthe radiation imaging system 100 shown in FIG. 1 except that a radiationdetector 302 for detecting a radiation irradiation state and an avibration measurement device 301 for measuring the vibration state of agrid 104 are prepared in an imaging device 110.

The same reference numerals as in the radiation imaging system 100 shownin FIG. 1 denote the same parts in the radiation imaging system 300shown in FIG. 4, and a detailed description thereof will be omitted.Only parts different from the radiation imaging system 100 in FIG. 1will be described in detail.

FIG. 5 is a flow chart showing operation control processing executed bya control device 111 of this embodiment for the system 300. FIGS. 6A to6H are timing charts showing the operation control timing.

The same step numbers as in the flow chart of FIG. 2 denote the sameprocessing steps in the flow chart of FIG. 5, and a detailed descriptionthereof will be omitted.

Step S201

The control device 111 recognizes an irradiation time T exp, the type ofsensor 106 used for imaging, and the type of radiation tube 101 on thebasis of imaging conditions selectively input by the user through animaging condition instruction device 115.

In accordance with the recognized information, the control device 111determines control until radiation irradiation and control afterradiation irradiation by processing from step S202.

Step S202

The control device 111 determines a sensor initialization time Tss inaccordance with the type of sensor 106.

Step S203′

The control device 111 determines a grid initialization time Tgs (timeuntil the grid 104 reaches the target moving speed and position) fromthe irradiation time T exp.

Step S204′

The control device 111 determines a pre-irradiation delay time Txs (timeafter radiation irradiation permission is instructed to a radiationgenerator 117 until the radiation generator 117 actually startsradiation irradiation) on the basis of the type of radiation tube 101.

Step S205

The control device 111 determines an irradiation delay time T1 (thelongest time of the sensor initialization time Tss, grid initializationtime Tgs, and pre-irradiation delay time Txs).

Step S206

The control device 111 determines, as a time table before irradiation,the initialization timing of the sensor 106 as “Tl−Tss”, the drive starttiming of the grid 104 as “Tl−Tgs”, and the radiation irradiationinstruction (irradiation permission) timing for the radiation generator117 as “Tl−Txs”.

Step S207

After control before radiation irradiation is control parameters aredetermined in the above-described way, the control device 111 determineswhether an imaging request is input by the user through an imagingbutton 116 and stands by until an imaging request is received.

Step S208

Upon recognizing that an imaging request is input by the user throughthe imaging button 116, the control device 111 executes operationcontrol according to the time table determined in step S206.

Initialization of the sensor 106 is started after the elapse of“Tl−Tss”, drive the driving of the grid 104 is started after the elapseof “Tl−Tgs”, and irradiation permission is executed after the elapse of“Tl−Txs”.

Step S209′

The control device 111 determines on the basis of a detection signaloutput from the radiation detector 302 whether radiation irradiation bythe radiation generator 117 is ended.

Step S210

Upon recognizing that radiation irradiation by the radiation generator117 is ended, the control device 111 stops driving the grid 104 througha grid moving section 108.

Step S211′

The control device 111 determines on the basis of a measurement resultfrom the vibration measurement device 301 whether the vibration of thegrid 104 has converged.

Step S212

When recognizing that the vibration of the grid 104 has converged, thecontrol device 111 causes a signal reading section 107 to start readingthe signal accumulated in the sensor 106.

In the operation control for the radiation imaging system 300 shown inthe flow chart of FIG. 5, especially when the end of radiationirradiation is recognized in accordance with the detection result fromthe radiation detector 302, drive the driving of the grid 104 isstopped. For this reason, the influence of electromagnetic noisegenerated from the grid moving section 108 can be prevented.

Furthermore, since the operation stands until it is determined on thebasis of the measurement result from the vibration measurement device301 that the vibration of the grid 104 has converged after the stop ofdrive stopping the driving of the grid 104, the influence of devicevibration can be prevented.

Hence, after the imaging request from the user is recognized, thecontrol device 111 controls the operation of the system 300 inaccordance with the flow chart in FIG. 5, thereby acquiring asatisfactory image.

The above operation control for the radiation imaging system 300 will bedescribed below in more detail with reference to the timing charts shownin FIGS. 6A to 6H.

The timing charts of FIGS. 6A to 6H explain timings after the imagingbutton 116 is pressed.

In accordance with the imaging conditions input by the user, forexample,

-   -   Irradiation time T exp=100 ms    -   Sensor initialization time Tss=200 ms    -   Grid initialization time Tgs=300 ms    -   Pre-irradiation delay time Txs=100 ms are determined.

In this case, the irradiation delay time T1 as the longest time of thesensor initialization time Tss, grid initialization time Tgs, andpre-irradiation delay time Txs is determined byT1=max(Tss, Tgs, Txs)=Tgs=300 ms

Operation control until radiation irradiation is determined from theseinitial conditions.

Next, control timings for sensor initialization, start of grid movement,and irradiation permission instruction after recognition of the imagingrequest are determined by subtracting a corresponding time required foroperation from the irradiation delay time T1.Sensor initialization timing: T1−Tss=100 msGrid movement start timing: T1−Tgs=0 msIrradiation enable signal transmission timing: T1−Txs=200 ms

After the control timings are determined, an imaging request (FIG. 6A)input by the user by pressing the imaging button 116 is waited upon.

When an imaging request is recognized, operation control for theradiation imaging system 300 is started on the basis of the determinedcontrol timings.

First, movement (motion) of the grid 104 is started, as shown in FIG.6B. Simultaneously, the vibration detection signal representing that thegrid 104 is in a moving state is set at High level, as shown in FIG. 6G.

The moving speed of the grid 104 acceleratingly increases and reaches anirradiation enable state after the elapse of 300 ms (grid initializationtime Tgs=300 ms), as shown in FIG. 6C.

Next, as shown in FIG. 6H, after the elapse of 100 ms (sensorinitialization timing: TI−Tss=100 ms) from imaging request recognition,initialization of the sensor 106 is started. After the elapse of 200 ms(sensor initialization time Tss=200 ms), initialization of the sensor106 is ended.

As shown in FIG. 6D, after the elapse of 200 ms (irradiation enablesignal transmission timing: Tl−Txs=200 ms) from imaging requestrecognition, the radiation generator 117 is instructed to startirradiation.

The radiation generator 117 starts actual irradiation after the elapseof 100 ms (pre-irradiation delay time Txs=100 ms), as shown in FIG. 6E.Simultaneously, the radiation detection signal representing radiationirradiation is set at High level, as shown in FIG. 6F.

When radiation irradiation is ended, and the output from the radiationdetector 302 becomes smaller than a predetermined threshold value, it isdetermined that irradiation is ended. As shown in FIG. 6F, the radiationdetection signal is set at Low level. Along with this processing,movement control for the grid 104 is stopped, as shown in FIG. 6B. Themoving speed of the grid 104 gradually decreases. The vibration state ofthe grid 104 at this time is observed by the vibration measurementdevice 301.

When the vibration of the imaging device 110, that is generated bymoving the grid 104, starts converging, and it is recognized that theoutput from the vibration measurement device 301 becomes smaller than apredetermined vibration amount, the vibration detection signal is set atLow level, as shown in FIG. 6G.

As shown in FIG. 6F, the signal reading section 107 is instructed to endsignal accumulation in the sensor 106 and start reading the signal.

At this time, the vibration of the imaging device 110 has become sosmall that it does not affect the image quality. As a result, asatisfactory image can be obtained.

The object of the present invention is achieved even by supplying astorage medium which stores software program codes for implementing thefunctions of the host and terminal in accordance with the first andsecond embodiments to in a system or apparatus and causing the computer(or a CPU or MPU) of the system or apparatus to read and execute theprogram codes stored in the storage medium.

In this case, the program codes read from the storage medium implementthe functions of the first and second embodiments by themselves, and thestorage medium which stores the program codes constitutes the presentinvention.

As a storage medium for supplying the program codes, for example, a ROM,a floppy disk, hard disk, optical disk, magnetooptical disk, CD-ROM,CD-R, magnetic tape, non-volatile memory card or the like can be used.

The functions of the first and second embodiments are implemented notonly when the readout program codes are executed by the computer butalso when the operating system (OS) running on the computer performspart or all of actual processing on the basis of the instructions of theprogram codes.

The functions of the first and second embodiments are also implementedwhen the program codes read from the storage medium are written in thememory of a function expansion board inserted into the computer or afunction expansion unit connected to the computer, and the CPU of thefunction expansion board or function expansion unit performs part or allof actual processing on the basis of the instructions of the programcodes.

As described above, according to the above embodiments, since the gridis stopped before the read of reading of the signal accumulated in theimage sensing element is started, the influence of electromagnetic noisedue to grid movement can be eliminated. Hence, no noise is superposed onthe image (radiation image or the like) obtained from the read signalfrom the image sensing element, and a high-quality image can beobtained.

When a predetermined standby time is set from the stop of the grid, thesignal read from the image sensing element starts after the influence ofvibration of the imaging element due to grid movement is reduced. Forthis reason, an image with a higher quality can be obtained.

Hence, the quality of the image can be prevented from degrading due tothe influence of electromagnetic noise upon grid movement. In addition,the quality of the image can be prevented from degrading due to theinfluence of vibration of the image sensing element upon grid movement.

For example, when the above embodiments are applied to radiationimaging, a satisfactory radiation image free from noise can be provided.For this reason, a diagnostic error in image diagnosis can be reliablyprevented.

(Third Embodiment)

FIG. 7 is a block diagram showing the arrangement of an X-ray imagesensing system according to the third embodiment of the presentinvention.

Reference numeral 10 denotes an X-ray room; 12, an X-ray control room;and 14, a diagnosis room.

The X-ray control room 12 has a system controller 20 for controlling theentire operation of the X-ray image sensing system. An operatorinterface 22 having an X-ray exposure request switch, touch panel,mouse, keyboard, joystick, foot switch, and the like is used by anoperator 21 to input various instructions to the system controller 20.The contents of instructions by the operator 21 are, e.g., imagingconditions (still/moving image, X-ray tube voltage, tube current, andX-ray irradiation time), imaging timing, image processing conditions, IDof a patient, and processing method for a read image. An image sensingcontroller 24 controls the X-ray image sensing system placed in theX-ray room 10. An image processor 26 processes an image obtained by theX-ray image sensing system in the X-ray room 10. Image processing by theimage processor 26 includes, e.g., image data correction, spacefiltering, recursive processing, gray-scale processing, scattered raycorrection, and dynamic range (DR) compression processing.

A large-capacity high-speed storage device 28 stores basic image dataprocessed by the image processor 26 and is formed from, e.g., a harddisk array such as a RAID. A monitor display (to be referred to as amonitor hereinafter) 30 displays an image. A display controller 32controls the monitor 30 to make it display various characters andimages. Reference numeral 34 denotes a large-capacity external storagedevice (e.g., a magnetooptical disk). A LAN board 36 connects the X-raycontrol room 12 to the diagnosis room 14 to transfer, e.g., an imageobtained in the X-ray room 10 to the apparatus in the diagnosis room 14.

An X-ray generator 40 for generating X-rays is placed in the X-ray room10. The X-ray generator 40 comprises an X-ray tube 42 for generatingX-rays, a high-voltage source 44 controlled by the image sensingcontroller 24 to drive the X-ray tube 42, and an X-ray stop 46 forconverging an X-ray beam generated by the X-ray tube 42 to a desiredimage sensing region. A patient 50 as an object to be examined lies onan imaging bed 48. The imaging bed 48 is driven in accordance with acontrol signal from the image sensing controller 24 so that thedirection of the patient 50 with respect to the X-ray beam from theX-ray generator 40 can be changed. An X-ray detector 52 for detectingthe X-ray beam transmitted through the patient 50 and the imaging bed 48is placed under the imaging bed 48.

The X-ray detector 52 comprises a stack of a grid 54, scintillator 56,photodetector array 58, and X-ray exposure amount monitor 60, and adriver 62 for driving the photodetector array 58. The grid 54 isarranged to reduce the influence of X-ray scattering caused when theX-rays are transmitted through the patient 50. The grid 54 is formedfrom an X-ray non-absorbing member and X-ray absorbing member and has astripe structure of, e.g., Al and Pb. In X-ray irradiation, to preventmoire by the matrix ratio relationship between the photodetector array58 and the grid 54, the X-ray detector 52 vibrates the grid 54 inaccordance with a control signal from the driver 62 on the basis ofsettings from the image sensing controller 24.

In the scintillator 56, the matrix substance of phosphor is excited(absorbed) by high-energy X-rays, and fluorescent light in the visibleregion is generated by the recombination energy. That is, the X-rays areconverted into visible light.

The fluorescent light is generated by the matrix itself such as CaWo₄ orCdWo₄ or luminescence center substance such as CsI:Tl or ZnS:Ag dopedinto the matrix. The photodetector array 58 converts the visible lightobtained by the scintillator 56 into an electrical signal.

The X-ray exposure amount monitor 60 is arranged in order to monitor theX-ray transmission amount. The X-ray exposure amount monitor 60 maydirectly detect X-rays using a silicon crystal light-receiving elementor the like, or detect fluorescent light generated by the scintillator56. In this embodiment, the X-ray exposure amount monitor 60 is formedfrom an amorphous silicon light-receiving element formed on the lowersurface of the substrate of the photodetector array 58, detects visiblelight (proportional to the X-ray dose) transmitted through thephotodetector array 58, and transmits the light amount information tothe image sensing controller 24. The image sensing controller 24controls the X-ray generator 40 on the basis of the information from theX-ray exposure amount monitor 60 to adjust the X-ray dose.

The driver 62 drives the photodetector array 58 under the control of theimage sensing controller 24 to read a signal from each pixel. Operationsof the photodetector array 58 and driver 62 will be described later indetail.

In the diagnosis room 14, an image processing terminal 70 for processingan image from the LAN board 36 or assisting the diagnosis, a videodisplay monitor 72 for outputting an image (moving image/still image)from the LAN board 36, an image printer 74, and a file server 76 forstoring image data are prepared.

A control signal from the system controller 20 to each device can begenerated by an instruction from the operator interface 22 in the X-raycontrol room 12 or the image processing terminal 70 in the diagnosisroom 14.

Basic operation of the system controller 20 will be described next.

On the basis of an instruction from the operator 21, the systemcontroller 20 outputs an imaging condition instruction to the imagesensing controller 24 for controlling the sequence of the X-ray imagesensing system. On the basis of the instruction, the image sensingcontroller 24 drives the X-ray generator 40, imaging bed 48, and X-raydetector 52 to obtain an X-ray image. The X-ray image signal output fromthe X-ray detector 52 is supplied to the image processor 26, subjectedto image processing designated by the operator 21, displayed on themonitor 30 as an image, and simultaneously, stored in the storage device28 as basic image data. The system controller 20 also executes imagere-processing and display of its result, image data transfer to a deviceon the network, storage, video display, and film printing on the basisof instructions from the operator 21.

Basic operation of the system shown in FIG. 7 will be described inaccordance with the signal flow.

The high-voltage source 44 of the X-ray generator 40 applies a highvoltage for generating X-rays to the X-ray tube 42 in accordance with acontrol signal from the X-ray tube 42. The X-ray tube 42 generates anX-ray beam. The patient 50 as an object to be examined is irradiatedwith the generated X-ray beam through the X-ray stop 46. The X-ray stop46 is controlled by the image sensing controller 24 in accordance withthe position where the object is to be irradiated with the X-ray beam.That is, the X-ray stop 46 shapes the X-ray beam as the image sensingregion changes so as not to perform unnecessary X-ray irradiation.

The X-ray beam output from the X-ray generator 40 passes through thepatient 50 who lies on the imaging bed 48 transparent to X-rays, and theimaging bed 48 and enters the X-ray detector 52. The imaging bed 48 iscontrolled by the image sensing controller 24 such that the X-ray beampasses through the object to be examined at different portions or indifferent directions.

The grid 54 of the X-ray detector 52 reduces the influence of X-rayscattering caused by passing the X-ray beam through the patient 50. Toprevent moire by the matrix ratio relationship between the photodetectorarray 58 and the grid 54, the image sensing controller 24 vibrates thegrid 54 in X-ray irradiation. In the scintillator 56, the matrixsubstance of phosphor is excited (absorbs the X-rays) by the high-energyX-rays, and fluorescent light in the visible region is generated by therecombination energy generated at that time. The photodetector array 58arranged adjacent to the scintillator 56 converts the fluorescent lightgenerated by the scintillator 56 into an electrical signal. That is, thescintillator 56 converts the X-ray image into a visible light image, andthe photodetector array 58 converts the visible light image into anelectrical signal. The X-ray exposure amount monitor 60 detects thevisible light (proportional to the X-ray dose) transmitted through thephotodetector array 58 and supplies the detection amount information tothe image sensing controller 24. The image sensing controller 24controls the high-voltage source 44 on the basis of the X-ray exposureamount information to cut off or adjust the X-rays. The driver 62 drivesthe photodetector array 58 under the control of the image sensingcontroller 24 to read a pixel signal from each photodetector. Details ofthe photodetector array 58 and driver 62 will be described later.

The pixel signal output from the X-ray detector 52 is supplied to theimage processor 26 in the X-ray control room 12. Since large noise isgenerated by X-ray generation in the X-ray room 10, the signaltransmission path from the X-ray detector 52 to the image processor 26must be highly resistant to noise. More specifically, a digitaltransmission system having an advanced error correction function or ashielded twisted pair line or optical fiber by a differential driver ispreferably used.

Although details will be described later, the image processor 26switches the image signal display format on the basis of an instructionfrom the system controller 20, executes image signal correction, spacefiltering, and recursive processing in real time, and also can executegrayscale processing, scattered ray correction, and DR compressionprocessing. The image processed by the image processor 26 is displayedon the screen of the monitor 30.

Simultaneously with real-time image processing, image information (basicimage) that has undergone only image correction is stored in the storagedevice 28. The image information stored in the storage device 28 isreconstructed to satisfy a predetermined standard (e.g., Image Save &Carry (IS&C)) and stored in the external storage device 34 and a harddisk in the file server 76 on the basis of an instruction from theoperator 21.

The devices in the X-ray control room 12 are connected to a LAN (or WAN)through the LAN board 36.

A plurality of X-ray image sensing systems can be connected to the LAN.The LAN board 36 outputs image data in accordance with a predeterminedprotocol (e.g., Digital Imaging and Communications in Medicine (DICOM)).By displaying the X-ray image on the screen of the monitor 72 connectedto the LAN as a high-resolution still image or moving image, real-timeremote diagnosis by a doctor is possible almost simultaneously withX-ray imaging.

FIG. 8 is a circuit diagram showing an equivalent circuit of aconstruction unit of the photodetector array 58.

One element is formed from a photodetection section 80 and a switchingthin film transistor (TFT) 82 for controlling charge accumulation andread reading and is generally formed from amorphous silicon (a-Si) on aglass substrate. The photodetection section 80 is formed from a parallelcircuit of a photodiode 80a and capacitor 80b, and a capacitor 80cconnected in series with the capacitor 80b. Charges by the photoelectricconversion effect are described as a constant current source 81. Thecapacitor 80b may be either the parasitic capacitance of the photodiode80a or an additional capacitor for improving the dynamic range of thephotodiode 80a. The common bias electrode (to be referred to as a Delectrode hereinafter) of the photodetection section 80 is connected toa bias power supply 84 through a bias line Lb. An electrode (to bereferred to as a G electrode hereinafter) on the side of the switchingTFT 82 of the photodetection section 80 is connected to a capacitor 86and charge reading preamplifier 88 through the switching TFT 82. Theinput to the preamplifier 88 is also connected to ground through a resetswitch 90 and signal line bias power supply 91.

Device operation of the photodetection section 80 will be described withreference to FIGS. 9A to 9C.

FIGS. 9A and 9B are views showing the energy band of a photoelectricconversion element that exhibits the refresh and photoelectricconversion mode operations of this embodiment. FIGS. 9A and 9B showstates in the direction of thickness of each layer. A lower electrode (Gelectrode) 301 is formed from Cr. An insulating layer 302 is formed fromSiN and inhibits both electrons and holes from passing. The thickness ofthe insulating layer 302 is set to be 50 nm or more such that electronsand holes cannot move by the tunnel effect. A photoelectric conversionsemiconductor layer 303 is formed from an intrinsic semiconductor layerof hydrogenated amorphous silicon a-Si. An injection inhibiting 304 isformed from an n-type a-Si layer for inhibiting holes from beinginjected into the photoelectric conversion semiconductor layer 303. Anupper electrode (D layer) 305 is formed from Al. In this embodiment, theD electrode does not completely cover the n-layer. However, sinceelectrons freely move between the D electrode and the n-layer, the Delectrode and n-layer always have an equipotential state. The followingdescription will be made assuming this. This photoelectric conversionelement performs two types of operation: refresh mode and photoelectricconversion mode in accordance with the manner the voltage is applied tothe D and G electrodes.

Referring to FIG. 9A, a potential negative with respect to the Gelectrode is applied to the D electrode. Holes represented by solid dotsin the mode shown in FIG. 9B is held for a certain period, the statereturns to the refresh mode shown in FIG. 9A again. The holes that arestaying in the i-layer 303 are moved to the D electrode, as describedabove, and simultaneously, a current corresponding to the holes flows.The number of holes corresponds to the total amount of light incidentduring the photoelectric conversion mode period. At this time, a currentcorresponding to the number of electrons injected into the i-layer 303also flows. The number of electrons is almost constant and is detectedby subtraction. That is, the photoelectric conversion element of thisembodiment can output the amount of light incident in real time andsimultaneously output the total amount of light incident for a givenperiod.

However, when the period of the photoelectric conversion mode becomeslong due to some reason, or the illuminance of incident light is high,no current may flow although light is incident. This is because a numberof holes stay in the i-layer 303 and are recombined with holes in thei-layer 303, as shown in FIG. 9C. If the light incident state changes inthis state, a current may unstably flow. When the mode is returned tothe refresh mode, the holes in the i-layer 303 are swept, and a currentproportional to light flows again in the next photoelectric conversionmode.

In the above description, in sweeping holes in i-layer 303 are moved tothe D electrode by the electric field. Simultaneously, electronsrepresented by hollow dots are injected into the i-layer 303. At thistime, some holes and electrons are recombined in the n-layer 304 andi-layer 303 and disappear. When this state continues for a sufficientlylong time, the holes in the i-layer 303 are swept from the i-layer 303.

To change this state to the photoelectric conversion mode shown in FIG.9B, a potential positive with respect to the G electrode is applied tothe D electrode. Electrons in the i-layer 303 are instantaneously movedto the D electrode. However, holes are not moved to the i-layer 303because the n-layer 304 acts as an injection inhibiting layer. Whenlight becomes incident on the i-layer 303 in this state, the light isabsorbed to generate electron-hole pairs. The electrons are moved to theD electrode by the electric field, and the holes move through thei-layer 303 and reach the interface between the i-layer 303 and theinsulating layer 302. However, since the holes cannot enter theinsulating layer 302 and move to the interface to the insulating layer302 in the i-layer 303, a current flows from the G electrode to maintainthe electrical neutrality. This current corresponds to the electron-holepairs generated by the light and is therefore proportional to theincident light. After the state in the photoelectric conversion thei-layer 303 in the refresh mode, it is ideal to sweep all holes.However, even when some holes are extracted, an effect can be obtained,and a current equal to that described above can be obtained without anyproblem. That is, it is only necessary to prevent the state shown inFIG. 9C in the detection opportunity in the next photoelectricconversion mode, and it suffices to determine the potential of the Delectrode with respect to the G electrode in the refresh mode, theperiod of the refresh mode, and the characteristics of the n-layer 304as an injection inhibiting layer. Electron injection into the i-layer303 in the refresh mode is not a necessary condition. The potential ofthe D electrode with respect to the G electrode is not limited to anegative potential. When a number of holes stay in the i-layer 303, theelectric field in the i-layer 303 is applied in a direction to move theholes to the D electrode even when the potential of the D electrode ishigher than that of the G electrode. For the characteristics of then-layer 304 as an injection inhibiting layer as well, the capability ofinjecting electrons into the i-layer 303 is not a necessary condition.

Referring back to FIG. 8, the signal read from one pixel will bedescribed.

First, the switching TFT 82 and reset switch 90 are temporarily turnedon to set the bias power supply 84 at a potential in the refresh mode.After the capacitors 80b and 80c are reset, the bias power supply 84 isset at a potential in the photoelectric conversion mode, and theswitching TFT 82 and reset switch 90 are sequentially turned off. Afterthat, X-rays are generated to irradiate the patient 50. The scintillator56 converts the X-ray image transmitted through the patient 50 into avisible light image. The photodiode 80a is turned on by the visiblelight image to discharge the capacitor 80b. The switching TFT 82 isturned on to connect the capacitors 80b and 86. Information in thecapacitor 80c is also transmitted to the capacitor 86. The voltage bycharges accumulated in the capacitor 86 is amplified by the preamplifier88, or the charges are converted into a voltage by a capacitor 89indicated by the dotted line, and the voltage is externally output.

FIG. 10 is a circuit diagram showing another equivalent circuit of aconstruction unit of the photodetector array 58.

One element is formed from the photodetection section 80 and switchingthin film transistor (TFT) 82 for controlling charge accumulation andread reading and is generally formed from amorphous silicon (a-Si) on aglass substrate. The photodetection section 80 is formed from theparallel circuit of the photodiode 80a and capacitor 80b. Charges by thephotoelectric conversion effect are described as the constant currentsource 81. The capacitor 80b may be either the parasitic capacitance ofthe photodiode 80a or an additional capacitor for improving the dynamicrange of the photodiode 80a. The cathode of the photodetection section80 (photodiode 80a) is connected to a bias power supply 85 through thebias line Lb as a common electrode (D electrode). The anode of thephotodetection section 80 (photodiode 80a) is connected from the gateelectrode (G electrode) to the capacitor 86 and charge readingpreamplifier 88 through the switching TFT 82. The input to thepreamplifier 88 is also connected to ground through the reset switch 90and signal line bias power supply 91.

First, the switching TFT 82 and reset switch 90 are temporarily turnedon to reset the capacitor 80b. Then, the switching TFT 82 and resetswitch 90 are turned off. After that, X-rays are generated to irradiatethe patient 50. The scintillator 56 converts the X-ray image transmittedthrough the patient 50 into a visible light image. The photodiode 80a isturned on by the visible light image to discharge the capacitor 80b. Theswitching TFT 82 is turned on to connect the capacitors 80b and 86.Information of the discharge amount of the capacitor 80b is alsotransmitted to the capacitor 86. The voltage by charges accumulated inthe capacitor 86 is amplified by the preamplifier 88, or the charges areconverted into a voltage by the capacitor 89 indicated by the dottedline, and the voltage is externally output.

Photoelectric conversion operation when the photoelectric conversionelement shown in FIG. 9 or 10 is expanded to a two-dimensional arraywill be described next. FIG. 11 is a schematic view showing theequivalent circuit of the photodetector array 58 having photoelectricconversion elements arranged in a two-dimensional array.

Two-dimensional read operation is the same as in the above two types ofequivalent circuits, and FIG. 11 shows an arrangement using theequivalent circuit shown in FIG. 10.

The photodetector array 58 is formed from about 2,000×2,000 to4,000×4,000 pixels, and the array area is about 200 mm×200 mm to 500mm×500 mm. Referring to FIG. 11, the photodetector array 58 is formedfrom 4,096×4,096 pixels, and the array area is 430 mm×430 mm. Hence, thesize of one pixel is about 105 μm×105 μm. In this case, 4,096 pixelsarranged in the horizontal direction form one block, and 4,096 blocksare arranged in the vertical direction to obtain a two-dimensionalstructure.

Referring to FIG. 11, the photodetector array having 4,096×4,096 pixelsis formed from one substrate. However, four photodetector arrays eachhaving 2,048×2,048 pixels may be combined. In this case, althoughcombining the four photodetector arrays is time-consuming, the yield ofeach photodetector array improves, and the total yield also improves.

As described with reference to FIGS. 8 and 10, one pixel is formed fromone photodetection section 80 and switching TFT 82. Each ofphotoelectric conversion elements PD (1,1) to (4096,4096) corresponds tothe photodetection section 80, and each of transfer switches SW (1,1) to(4096,4096) corresponds to the switching TFT 82. The gate electrode (Gelectrode) of a photoelectric conversion element PD (m,n) is connectedto a common column signal line Lcm for that column through acorresponding switch SW (m,n). For example, the photoelectric conversionelements PD (1,1) to (4096,1) of the first column are connected to afirst column signal line Lc1. All the common electrodes (D electrodes)of the photoelectric conversion elements PD (m,n) are connected to thebias power supply 85 through the bias line Lb.

Control terminals of the switches SW (m,n) of the same row are connectedto a common row selection line Lrn. For example, the switches SW (1,1)to (1,4096) of the first row are connected to a row selection line Lr1the. The row selection lines Lr1 to Lr4096 are connected to the imagesensing controller 24 through a line selector 92. The line selector 92is constituted by an address decoder 94 which decodes a control signalfrom the image sensing controller 24 and determines a specificphotoelectric conversion element from which the signal charges are to beread, and 4,096 switch elements 96 turned on/off in accordance with theoutput from the address decoder 94. With this arrangement, signalcharges can be read from the photoelectric conversion element PD (m,n)connected to the switch SW (m,n) connected to the arbitrary line Lrn. Asthe simplest structure of the line selector 92, it may be constructed bya shift register used in, e.g., a liquid crystal display.

The column signal lines Lc1 to Lc4096 are connected to a signal readcircuit 100 controlled by the image sensing controller 24. In the signalread circuit 100, reset switches 102-1 to 102-4096 reset the columnsignal lines Lc1 to Lc4096 to a reset reference potential 101.Preamplifiers 106-1 to 106-4096 amplify signal potentials from thecolumn signal lines Lc1 to Lc4096. Sample-and-hold (S/H) circuits 108-1to 108-4096 sample and hold the outputs from the preamplifiers 106-1 to106-4096. An analog multiplexer 110 multiplexes the outputs from thesample-and-hold circuits 108-1 to 108-4096 on the time axis. An A/Dconverter 112 converts the analog output from the multiplexer 110 into adigital signal. The output from the A/D converter 112 is supplied to theimage processor 26.

In the photodetector array shown in FIG. 11, 4,096×4,096 pixels aredivided into 4,096 columns by the column signal lines Lc1 to Lc4096, andsignal charges are simultaneously read from 4,096 pixels per row,transferred to the analog multiplexer 110 through the column signallines Lc1 to Lc4096, preamplifiers 106-1 to 106-4096, and S/H circuits108-1 to 108-4096, multiplexed on the time axis, and sequentiallyconverted into a digital signal by the A/D converter 112.

Referring to FIG. 9, the signal read circuit 100 has only one A/Dconverter 112. Actually, A/D conversion is simultaneously executed byfour to 32 systems. This is because the image signal read time must beshortened without unnecessarily increasing the analog signal band andA/D conversion rate. The signal charge accumulation time and A/Dconversion time have a close relationship. When high-speed A/Dconversion is performed, the band of the analog circuit widens, and adesired S/N ratio can hardly be attained. Normally, the image signalread time need be shortened without unnecessarily increasing the A/Dconversion speed. To do this, a number of A/D converters are used toA/D-convert the output from the multiplexer 110. However, the larger thenumber of A/D converters is, the higher the cost becomes. Consideringthe above points, an appropriate number of A/D converters are used.

Since the X-ray irradiation time is about 10 to 500 msec, the fullscreen read time or charge accumulation time is appropriately set on theorder of 100 msec or relatively short.

For example, to sequentially drive all pixels to read an image, theanalog signal band is set to about 50 MHz, and A/D conversion isperformed at a sampling rate of, e.g., 10 MHz. In this case, at leastfour A/D converters are required. In this embodiment, A/D conversion issimultaneously performed by 16 systems. The outputs from the 16 A/Dconverters are input to 16 corresponding memories (e.g., FIFO) (notshown). By selectively switching the memories, image data correspondingto one continuous scanning line is transferred to the image processor26.

FIG. 12 is a schematic timing chart of the sensor read. Two-dimensionaldrive in sensing a still image by X-ray irradiation of one cycle will bedescribed with reference to FIGS. 11 and 12.

Reference numeral 601 schematically denotes an X-ray exposure requestcontrol signal; 602, an X-ray exposure state; 603, a current in thecurrent source 81 in the sensor; 604, a control state of the rowselection line Lrn; and 605, an analog input to the A/D converter 112.

In the equivalent circuit sensor shown in FIG. 8, first, the driver 62sets the bias line to a bias value Vr in the refresh mode, connects allthe column signal lines Lc1 to Lc4096 to the reset reference potential101 to initialize them to a predetermined bias value of the columnsignal lines Lc, and applies a positive voltage Vgh to all the rowselection lines Lr1 to Lr4096. The switches (1,1) to (4096,4096) areturned on to refresh the G electrodes of all the photoelectricconversion elements to Vbt and the D electrodes to Vr.

After that, the driver 62 sets the bias line Lb to a bias value Vs inthe photoelectric conversion mode, release all the column signal linesLc1 to Lc4096 from the reset reference potential 101, and applies avoltage Vg1 to all the row selection lines Lr1 to Lr4096 to turn off theswitches (1,1) to (4096,4096). The mode shifts to the photoelectricconversion mode.

Operation from here is common to the equivalent circuit sensors shown inFIGS. 8 and 10, and a description thereof will be commonly done. Whilekeeping the bias line at the bias value Vs in the photoelectricconversion mode, all the column signal lines Lc are connected to thereset reference potential 101 to reset the column signal lines. Afterthat, the positive voltage Vgh is applied to the row selection line Lr1to turn on the switches (1,1) to (1,4096) and reset the G electrodes ofthe photoelectric conversion elements of the first column to Vbt. Next,the row selection line Lr1 is set to the positive voltage Vg1 to turnoff the switches (1,1) to (1,4096).

All the pixels are reset by sequentially repeating row selection,thereby completing preparation for imaging. Since the above operation isthe same as the signal charge read operation except whether signalcharges are read, operation after this reset operation is called a“pre-read”. During this pre-read operation, all the row selection linesLr can be simultaneously set to Vgh. In this case, however, whenpreparation for the read is completed, the signal line potential islargely shifted from the reset voltage Vbt, and a signal with high S/Nradio can hardly be obtained. In the above-described example, the rowselection lines Lr1 to Lr4096 are reset in this order. However, they canbe reset in an arbitrary order under the control of the driver 62 on thebasis of the setting of the image sensing controller 24.

An X-ray exposure request is waited upon while repeating the pre-readoperation.

When an exposure request is generated, the pre-read operation isperformed again to prepare for image acquisition, and X-ray exposure iswaited. When preparation for image acquisition is completed, X-rayexposure is executed in accordance with an instruction from the imagesensing controller 24.

After X-ray exposure, signal charges are read from the photoelectricconversion elements 80. First, the voltage Vgh is applied to the rowselection line Lr of a certain row (e.g., Lr1) of the photoelectricconversion element array to output accumulated charge signals to thesignal lines Lc1 to Lc4096. Signals of 4,096 pixels are simultaneouslyread from the column signal lines Lc1 to Lc4096 in units of columns.

Next, the voltage Vgh is applied to another row selection line Lr (e.g.,Lr2) to output accumulated charge signals to the signal lines Lc1 toLc4096. Signals of 4,096 pixels are simultaneously read from the columnsignal lines Lc1 to Lc4096 in units of columns. All pieces of imageinformation are read by sequentially repeating this operation for the4,096 column signal lines.

During the operation, the charge accumulation time of each sensorcorresponds to a time after the reset operation is ended, i.e., the TFT82 in the pre-read mode is turned off until the TFT 82 is turned on toread charges. Hence, the accumulation time and timing change for eachrow selection.

After an X-ray image is read, a correction image is acquired. Thiscorrection data is necessary to acquire a high-quality image and is usedto correct the X-ray image. The basic image acquisition procedure is thesame as described above except that no X-ray exposure is performed. Thecharge accumulation time in reading the X-ray image equals that inreading the correction image.

When high-resolution image information is unnecessary, or the image dataread speed need be high, all pieces of image information need not alwaysbe read. In accordance with the imaging method selected by the operator21, the image sensing controller 24 sets a drive instruction ofthinning, pixel averaging, or region extraction for the driver 62.

To thin the image data, first, the row selection line Lr1 is selected,and in outputting signals from the column signal lines Lc, signalcharges are read from one column while incrementing, e.g., n of Lc2n−1(n: natural number) one by one from 0. After that, signals are read fromone row while incrementing m of Lr2m−1 (m: natural number) one by onefrom 1. In this example, the number of pixels is thinned to 1/4. Thedriver 62 thins the number of pixels to 1/9, 1/16, or the like inaccordance with a setting instruction from the image sensing controller24.

For pixel averaging, when the voltage Vgh is simultaneously applied torow selection lines Lr2m and Lr2m+1 during the above-describedoperation, TFTs 2m and 2n and TFTs 2m+1 and 2n are simultaneously turnedon, so that analog addition of two pixels in the column direction can beperformed. This means that not only addition of two pixels but alsoanalog addition of a puerility plurality of pixels in the column signalline direction can be easily performed. For addition in the rowdirection, when adjacent pixels (Lc2n and Lc2n+1) are digitally addedafter A/D conversion output, the sum of 2×2 square pixels can beobtained together with the above analog addition. Hence, the data can beread at a high speed without wasting the X-ray irradiation.

As another method of decreasing the total number of pixels to increasethe read speed, the image read region is limited. To do this, theoperator 21 inputs a necessary region from the operator interface 22,the image sensing controller 24 issues an instruction to the driver 62on the basis of the input region, and the driver 62 changes the dataread range and drives the two-dimensional detector array.

In this embodiment, in the high-speed read mode, 1,024×1,024 pixels areread at 30 F/S. That is, in the entire region of the two-dimensionaldetector array, addition processing of 4×4 pixels is performed to thinthe number of pixels to 1/16, and in the smallest range, an image issensed in a 1,024×1,024 range without thinning. With this image sensing,a digital zoom image can be obtained.

FIG. 13 is a timing chart including image sensing operation of the X-raydetector 52. The operation of the X-ray detector 52 will be describedmainly with reference to FIG. 13.

Reference numeral 701 denotes an image sensing request signal to theoperator interface 22; 702, an actual X-ray exposure state; 703, animaging request signal from the image sensing controller 24 to thedriver 62 on the basis of an instruction from the operator 21; 704, animaging ready signal of the X-ray detector 52; 705, a drive signal forthe grid 54; 706, a power control signal in the X-ray detector 52; 707,a driven state of the X-ray detector (especially charge read operationfrom the photodetector array 58); and 708, an image processing ordisplay state.

Until a detector preparation request or imaging request is input by theoperator 21, the driver 62 stands by in a power control off state, asindicated by 706. More specifically, referring to FIG. 11, the rowselection lines Lr, column signal lines Lc, and bias line Lb are kept atan equipotential state (especially signal GND level) by a switch (notshown), and no bias is applied to the photodetector array 58.Alternatively, power supply including the signal read circuit 100, lineselector 92, and bias power supply 84 or 85 may be cut off to keep therow selection lines Lr, column signal lines Lc, and bias line Lb at theGND potential.

In accordance with an imaging preparation request instruction (701: 1stSW) from the operator 21 to the operator interface 22, the image sensingcontroller 24 outputs an instruction to shift the X-ray generator 40 toan imaging ready state and shift the X-ray detector 52 to an imagingpreparation state. Upon receiving the instruction, the driver 62 appliesa bias to the photodetector array 58 and repeats (refresh and) pre-readFi. The request instruction is, e.g., the 1st SW of the exposure requestswitch to the X-ray generator (normally, rotor up for the tube or thelike is started) or, when a predetermined time (several sec or more) isrequired by the X-ray detector 52 for imaging preparation, aninstruction for starting preparation of the X-ray detector 52.

In this case, the operator 21 need not consciously issue the imagingpreparation request instruction to the X-ray detector 52. That is, whenpatient information or imaging information is input to the operatorinterface 22, the image sensing controller 24 may interpret it as adetector preparation request instruction and shift the X-ray detector 52to the detector preparation state.

In the detector preparation state, in the photoelectric conversion mode,to prevent a dark current from being gradually accumulated in thephotodetection section 80 after the pre-read and the capacitor 80b (80c)from being held in the saturated state, the (refresh R and) pre-read Fiis repeated at a predetermined interval. This driving performed in theperiod when no actual X-ray exposure request is generated although theimaging preparation request from the operator 21 has been received,i.e., driving in which the pre-read Fi performed in the detectorpreparation state is repeated at a predetermined time interval T1 willbe referred to as “idling drive” hereinafter. The period when the idlingdrive is performed in the detector preparation state will be referred toas an “idling drive period” hereinafter. How long the idling driveperiod continues is undefined in practical use. To minimize the readoperation with load on the photodetector array 58 (especially the TFTs82), the time interval T1 is set to be longer than that in the normalimaging operation, and the pre-read Fi dedicated to idling for which theON time of the TFTs 82 is shorter than that in a normal read drive Fr.For a sensor that requires the refresh R, the refresh R is performedonce for several times of pre-read Fi.

X-ray image acquisition mainly performed by the X-ray detector 52 willbe described next.

Drive of the X-ray detector 52 in acquiring an X-ray image is mainlycomprised of two image acquisition cycles. As indicated by 707, one isX-ray image acquisition drive, and the other is correction dark imageacquisition drive. The drive cycles are almost the same except whetherX-ray exposure operation is performed. Each drive cycle has three parts:an image sensing preparation sequence, charge accumulation (exposurewindow), and image read.

X-ray image acquisition will be described below in accordance with thesequence.

In accordance with an imaging request instruction (701: 2nd SW) from theoperator 21 to the operator interface 22, the image sensing controller24 controls imaging operation while synchronizing the X-ray generator 40with the X-ray detector 52. In accordance with the imaging requestinstruction (701: 2nd SW), an imaging request signal is assertedprovided to the X-ray detector at a timing represented by the X-rayexposure request signal 703. The driver performs predetermined imagesensing preparation sequence drive operations as indicated by theimaging driven state 707 in response to the imaging request signal. Morespecifically, if the refresh is necessary, the refresh is performed.Then, a pre-read FR dedicated to the imaging sequence is performed apredetermined number of times, and a pre-read Fpf dedicated to thecharge accumulation state is performed to shift the state to the chargeaccumulation state (image sensing window: T4).

The number of times and time interval T2 of the pre-read Fp for theimage sequence are based on values preset prior to the imaging requestfrom the image sensing controller 24. Optimum drive is automaticallyselected depending on the image sensing portion or whether the requestfrom the operator 21 represents priority on the operability or imagequality. A period (T3) from the exposure request to the end of imagingpreparation is required to be short in practical use. Hence, thepre-read Fp dedicated to the image sensing preparation sequence isperformed. In addition, independently of the state of idling drive, whenan exposure request is generated, the image sensing preparation sequencedrive is immediately started to shorten the period (T3) from theexposure request to the end of imaging preparation, thereby improvingthe operability.

In synchronism with the image sensing preparation of the photodetectorarray 58, the driver 62 starts moving the grid 54 to sense an imagewhile setting the grid in an optimum moving state in synchronism withthe actual X-ray exposure 702. In this case as well, the driver 62operates on the basis of an optimum grid moving start timing and optimumgrid moving speed that are set by the image sensing controller.

In this embodiment, to eliminate the influence of vibration by theoperation of the grid 54, the start of movement of the grid 54 iscontrolled such that a change in acceleration becomes small. Inaddition, in executing the pre-read Fpf dedicated to the chargeaccumulation state, which is readily affected by vibration, the grid 54is controlled to exhibit uniform motion (still state or motion atuniform speed).

When image sensing preparation of the X-ray detector 52 is ended, thedriver 62 returns the X-ray detector ready signal 704 to the imagesensing controller 24. On the basis of this signal transition, the imagesensing controller 24 asserts provides the X-ray generation requestsignal 702 to the X-ray generator 40. The X-ray generator 40 generatesX-rays while receiving the X-ray generation request signal 702. When apredetermined amount of X-rays is generated, the image sensingcontroller 24 negates the X-ray generation request signal 702, therebynotifying the X-ray detector 52 of the image acquisition timing. On thebasis of this timing, the driver 62 immediately stops the grid 54 andstarts operating the signal read circuit 100 that has been in thestandby state. After the OFF time of the grid 54 and a predeterminedwait time to stabilize the signal read circuit 100, when operation ofreading image data from the photodetector array 58 and acquiring a rawimage for the image processor 26 on the basis of the driver 62 is ended,the driver 62 shifts the signal read circuit 100 to the standby stateagain.

In this embodiment, to eliminate the influence of vibration by theoperation of the grid 54, the grid 54 is controlled to exhibit uniformmotion (including the still state) before drive of an X-ray imageacquisition frame Frxo that is most readily affected by vibration noise.Alternatively, a vibration sensor for measuring vibration may beattached to the X-ray detector 52, and the drive of the X-ray imageacquisition frame Frxo may be started after confirming that thevibration by the grid or other factors has converged to a predeterminedor less value.

Subsequently, the X-ray detector 52 acquires a correction image. Thatis, the above imaging sequence for imaging is repeated to acquire a darkimage without X-ray irradiation, and the correction dark image istransferred to the image processor 26.

In the image sensing sequence, the X-ray exposure time or the like mayslightly change between imaging cycles. However, when the same imagesensing sequence is reproduced, including such differences, to acquire arough image, an image with a higher quality can be obtained. However,the operation of the grid 54 is not limited to this. The grid 54 may beset still to suppress the influence of vibration in acquiring the roughimage. In this case, after the image is almost acquired, the grid 54 isinitialized at a predetermined timing that does not affect the imagequality.

FIG. 14 is a block diagram showing the flow of image data in the imageprocessor 26. Reference numeral 801 denotes a multiplexer for selectinga data path; 802 and 803, X-ray image and rough image frame memories;804, an offset correction circuit; 805, a gain correction data framememory; 806, a gain correction circuit; 807, a defect correctioncircuit; and 808, other image procession circuits.

An X-ray image acquired by the X-ray image acquisition frame Frxo inFIG. 13 is stored in the X-ray image frame memory 802 through themultiplexer 801. A correction image acquired in a correction imageacquisition frame Frno is stored in the dark image frame memory 803through the multiplexer 801.

When the images are almost stored, offset correction (e.g., Frxo−Frno)is performed by the offset correction circuit 804. Subsequently, thegain correction circuit 806 performs gain correction (e.g.,(Frxo−Frno)/Fg) using gain correction data Fg which is acquired andstored in the gain correction frame memory in advance. For the datatransferred to the defect correction circuit 807, the image iscontinuously interpolated not to generate any sense of incompatibilityat a dead pixel or connections between a plurality of panels of theX-ray detector 52, thus completing sensor-dependent correctionprocessing resulted from the X-ray detector 52. In addition, the imageprocession circuits 808 execute general image processing such asgrayscale processing, frequency processing, and emphasis processing.After that, the processed data is transferred to the display controller32, and the image is displayed on the monitor 30.

FIGS. 15 and 16 are views showing examples of the driving mechanism ofthe grid 54.

A frame 901 holds the grid 54. A cam mechanism 902 for vibrating theframe 901 is connected to a rotating mechanism such as a grid drivingmotor (not shown).

The grid driving motor (not shown) rotates and stops at the grid movingtiming shown in FIG. 13 in accordance with an instruction from thedriver 62, thereby moving the grid 54 in the direction indicated by thearrow or stopping the grid 54. An elastic member 1001 for moving thegrid is formed from, e.g., a spring. A mechanism 1002 for moving thegrid 54 to the home position is formed from, e.g., a solenoid. A brakingmechanism 1003 stops the grid 54. In the initialization operation, thesolenoid mechanism 1002 is operated to move the grid to the homeposition indicated by the broken line, and the grid is stopped by thebraking mechanism 1003. The grid 54 is moved by canceling the braking onthe basis of an instruction from the driver 62. The braking mechanism1003 stops the grid in accordance with an instruction from the driver 62at a predetermined timing.

As described above, according to the X-ray image sensing apparatus ofthis embodiment, a satisfactory image can be easily and reliablyobtained without any influence of vibration of the grid 54 or the likeby a very simple arrangement.

(Fourth Embodiment)

In this embodiment, the internal arrangement of an X-ray room 10 isalmost the same as in FIG. 7, and a description of common units will beomitted.

Reference numeral 48b denotes part of an imaging bed 48 and represents abed for a fluoroscopic system in FIG. 17. A fluoroscopic II (ImageIntensifier) 1101 is controlled by an image sensing controller 24 totransfer an acquired image to an image processor 26 and then display theimage on a monitor 30 or monitor dedicated to a fluoroscopic image, likean X-ray detector 52. The X-ray detector 52 is mainly located at aposition B during a fluoroscopic image acquisition period and mainlymoves to a position A during a simple image acquisition period. TheX-ray detector 52 is moved in accordance with an instruction from theimage sensing controller 24 to the imaging bed 48. The moving operationis performed by a mechanical means (not shown) for moving the X-raydetector 52.

FIG. 18 is a timing chart including image sensing operation of the X-raydetector 52. The operation of the X-ray detector 52 of this embodimentwill be described mainly with reference to FIG. 18.

FIG. 18 is almost the same as FIG. 13, and different points will bemainly explained.

Reference numeral 1201 denotes an image sensing request signal to anoperator interface 22, which represents a simple X-ray imaging requeststate in FIG. 13 but a fluoroscopic/simple imaging request in thisembodiment. Reference numeral 702 denotes an actual X-ray exposurestate; 703, an imaging request signal from the image sensing controller24 to a driver 62 on the basis of an instruction from an operator 21;704, an imaging ready signal of the X-ray detector 52; 705, a drivesignal for a grid 54; 706, a power control signal in the X-ray detector52; 707, a driven state of the X-ray detector (especially charge readoperation from a photodetector array 58); and 708, an image datatransfer state or an image processing or display state. In addition,reference numeral 1202 denotes an X-ray output state for X-rayfluoroscopy; 1203, a concept of moving speed of the X-ray detector 52;and 1204, a position of the X-ray detector 52.

While no request is received from the operator 21, the X-ray detector 52stands by at the position B of the imaging bed 48.

When a fluoroscopy request 1201 from the operator 21 is detected,fluoroscopic imaging is started (1202), and simultaneously, the X-raydetector 52 starts idling drive (707). When the operator 21 determinesthe object to be sensed and outputs a general imaging preparationrequest (1st SW: 1201), the X-ray generator 40 starts preparing forX-ray generation for general imaging and ends the preparation after apredetermined time. When the operator 21 inputs a general imagingrequest (2nd SW: 1201), the image sensing controller 24 starts X-rayimage acquisition drive, instructs the X-ray detector 52 to prepare forimaging (703), stops fluoroscopic imaging (1202), and starts moving theX-ray detector 52 (1203 and 1204).

In this embodiment, the image sensing controller 24 as a control meansperforms control such that the driver 62 operates the photodetectorarray 58 in a steady state with a converged vibration, i.e., at apredetermined speed (uniform speed) without acceleration during anoperation period related to the read of the X-ray detector 52 as adetection means.

At the start of moving, moving is started while continuously changingthe acceleration not to increase the vibration. Since a time T3 untilthe end of imaging preparation of the X-ray detector 52 is known inadvance, the X-ray detector 52 is completely moved to the generalimaging position A within a time according to the time T3. However, inthe driven state 707, when vibration occurs at the time of a frame Fpfimmediately before the end of imaging preparation, noise is readilysuperposed on the image. To prevent this, immediately after the end ofthe frame Fpf, stop operation of the X-ray detector 52 is started, anduntil this time, the X-ray detector 52 is controlled to move at aconstant speed without generating any acceleration.

When preparation is ended, the X-ray exposure 702 is performed.Immediately after exposure is ended, an X-ray image acquisition frameFrxo is driven to acquire an X-ray image (707). After the end of X-rayexposure 702, fluoroscopic imaging should be started as soon aspossible. After the drive of the X-ray image acquisition frame Frxo isended, correction dark image acquisition drive is started, andsimultaneously, movement of the X-ray detector 52 from the position A tothe position B is immediately started (1204). As in the preceding X-rayimage acquisition drive, movement is started while continuously changingthe acceleration not to increase the vibration. Since the time T3 untilthe end of imaging preparation of the X-ray detector 52 is known inadvance, as in the X-ray image acquisition drive, the X-ray detector 52is completely moved to the general imaging position B within a timeaccording to the time T3. Contents related to the frame Fpf immediatelybefore the end of imaging preparation are also the same as in the X-rayimage acquisition drive. When movement from the position A to theposition B is ended, fluoroscopic imaging is resumed, and thefluoroscopic image can be redisplayed from this time. After that, arough image acquisition frame Frno is driven at a predetermined timingto acquire a rough image. The general image is subjected topredetermined image processing and then displayed on the monitor 30.

For the control, as in the third embodiment, a sensor (not shown)capable of detecting a vibration amount may be arranged in or near theX-ray detector 52, and a predetermined read (e.g., the X-ray imageacquisition frame Frxo, dark image acquisition frame Frno, or frame Fpfimmediately before the end of imaging preparation) may be started whenthe vibration becomes equal to or smaller than a predetermined value.

For the control, except a predicted period of vibration in the driver62, an operation period related to the image read of the X-ray detector52 may be set, and drive related to image acquisition may be performedduring this operation period.

As described above, according to the X-ray image sensing apparatus ofthis embodiment, a satisfactory image can be easily and reliablyobtained without any influence of vibration of the X-ray detector 52 orthe like by a very simple arrangement.

(Fifth Embodiment)

In this embodiment, the internal arrangement of an X-ray room 10 isalmost the same as in FIG. 7, and a description of common units will beomitted.

Reference numeral 48b denotes part of an imaging bed 48 and represents abed for a fluoroscopic system in FIG. 17. A fluoroscopic II (ImageIntensifier) 1101 is controlled by an image sensing controller 24 totransfer an acquired image to an image processor 26 and then display theimage on a monitor 30 or monitor dedicated to a fluoroscopic image, likean X-ray detector 52. The X-ray detector 52 is mainly located at aposition B during a fluoroscopic image acquisition period and mainlymoves to a position A during a simple image acquisition period. TheX-ray detector 52 is moved in accordance with an instruction from theimage sensing controller 24 to the imaging bed 48. The moving operationis performed by a mechanical means (not shown) for moving the X-raydetector 52.

FIG. 19 is a timing chart including image sensing operation of the X-raydetector 52. The operation of the X-ray detector 52 of this embodimentwill be described mainly with reference to FIG. 19.

FIG. 19 is almost the same as FIG. 13, and different points will bemainly explained.

Reference numeral 1201 denotes an image sensing request signal to anoperator interface 22, which represents a simple X-ray imaging requeststate in FIG. 13 but a fluoroscopic/simple imaging request in thisembodiment. Reference numeral 702 denotes an actual X-ray exposurestate; 703, an imaging request signal from the image sensing controller24 to a driver 62 on the basis of an instruction from an operator 21;704, an imaging ready signal of the X-ray detector 52; 705, a drivesignal for a grid 54; 706, a power control signal in the X-ray detector52; 707, a driven state of the X-ray detector (especially charge readoperation from a photodetector array 58); and 708, an image datatransfer state or an image processing or display state. In addition,reference numeral 1202 denotes an X-ray output state for X-rayfluoroscopy; 1203, a concept of moving speed of the X-ray detector 52;and 1204, a position of the X-ray detector 52.

While no request is received from the operator 21, the X-ray detector 52stands by at the position B of the imaging bed 48.

When a fluoroscopy request 1201 from the operator 21 is detected,fluoroscopic imaging is started (1202), and simultaneously, the X-raydetector 52 starts idling drive (707). When the operator 21 determinesthe object to be sensed and outputs general imaging preparation request(1st SW: 1201), the X-ray generator 40 starts preparing for X-raygeneration for general imaging and ends the preparation after apredetermined time. When the operator 21 inputs a general imagingrequest (2nd SW: 1201), the image sensing controller 24 starts X-rayimage acquisition drive, instructs the X-ray detector 52 to prepare forimaging (703), stops fluoroscopic imaging (1202), and starts moving theX-ray detector 52 (1203 and 1204).

In this embodiment, the image sensing controller 24 as a control meansperforms control such that the driver 62 operates the photodetectorarray 58 in a steady state with a converged vibration, i.e., at apredetermined acceleration during an operation period related to theread of the X-ray detector 52 as a detection means.

When a desired acceleration is obtained, the motion preferably shifts touniformly accelerated motion. In general control, actually, theacceleration abruptly changes (arrows in 1205). Since a time T3 untilthe end of imaging preparation of the X-ray detector 52 is known inadvance, the X-ray detector 52 is completely moved to the generalimaging position A within a time according to the time T3. When themovement and frame Fpf are synchronously ended, the time from the 2nd SWto the X-ray exposure 702 can be minimized. Hence, a frame Fpf isrequired to be ended at the time of predetermined deceleration (negativeacceleration). In the driven state 707, when vibration occurs at thetime of the frame Fpf immediately before the end of imaging preparation,noise is readily superposed on the image. To prevent this, the frame Fpfis acquired at a timing when the vibration due to the abrupt change inacceleration has converged, and the X-ray detector 52 is stoppedimmediately after the end of the frame Fpf.

When preparation is ended, the X-ray exposure 702 is performed. Afterthe end of X-ray exposure 702, fluoroscopic imaging should be started assoon as possible. Hence, movement of the X-ray detector 52 from theposition A to the position B is started immediately after the end ofexposure (1204). Simultaneously, the X-ray image acquisition frame Frxois driven at the time of uniform acceleration (or uniformly acceleratedmotion) at the timing when the vibration due to a change in accelerationconverges, thereby acquiring an X-ray image. After the end of the X-rayimage acquisition frame Frxo, correction dark image acquisition drive isstarted. Since the time T3 until the end of imaging preparation of theX-ray detector 52 is known in advance, as in the X-ray image acquisitiondrive, the X-ray detector 52 is completely moved to the general imagingposition B within a time according to the time T3. Contents related tothe frame Fpf immediately before the end of imaging preparation are alsothe same as in the X-ray image acquisition drive. When movement from theposition A to the position B is ended, fluoroscopic imaging is resumed,and the fluoroscopic image can be redisplayed from this time. Afterthat, a dark image acquisition frame Frno is driven at a predeterminedtiming to acquire a dark image. The general image is subjected topredetermined image processing and then displayed on the monitor 30.

For the control, as in the third embodiment, a sensor (not shown)capable of detecting a vibration amount may be arranged in or near theX-ray detector 52, and a predetermined read (e.g., the X-ray imageacquisition frame Frxo, dark image acquisition frame Frno, or frame Fpfimmediately before the end of imaging preparation) may be started whenthe vibration becomes equal to or smaller than a predetermined value.

For the control, except a predicted period of vibration in the driver62, an operation period related to the image read of the X-ray detector52 may be set, and drive related to image acquisition may be performedduring this operation period.

As described above, according to the X-ray image sensing apparatus ofthis embodiment, a satisfactory image can be easily and reliablyobtained without any influence of vibration of the X-ray detector 52 orthe like by a very simple arrangement.

Three embodiments, the third to fifth embodiments, have been describedabove. The present invention is applied to a cooling fan or any otherpotential vibration source.

The present invention also incorporates a case wherein to operatevarious devices to implement the functions of the above-describedembodiments, software program codes for implementing the functions ofthe embodiments are supplied to a computer in an apparatus or systemconnected to the devices, and the devices are operated in accordancewith a program stored in the computer (or CPU or MPU) of the system orapparatus.

In this case, the software program codes themselves implement thefunctions of the above-described embodiments, and the program codesthemselves and a means for supplying the program codes to the computer,e.g., a storage medium which stores such program codes constitute thepresent invention. As the storage medium for storing such program codes,for example, a floppy disk, hard disk, optical disk, magnetoopticaldisk, CD-ROM, magnetic tape, nonvolatile memory card, ROM, or the likecan be used.

The functions of the above-described embodiments are implemented whenthe supplied program codes are executed by the computer. In addition,even when the functions of the above-described embodiments arecooperatively implemented by an operating system (OS) running on thecomputer or another application software, the program codes are includedin the embodiments of the present invention.

The functions of the above-described embodiments are also implementedwhen the supplied program codes are stored in the memory of a functionexpansion board inserted into the computer or a function expansion unitconnected to the computer, and the CPU of the function expansion boardor function expansion unit performs part or all of actual processing onthe basis of the instructions of the program codes.

As has been described above, according to the third to fifthembodiments, a radiation image sensing apparatus (image sensingapparatus) and image sensing method which can easily and reliably obtaina satisfactory image without any influence of vibration or a grid orX-ray detection means by a very simple arrangement can be provided.

The present invention is not limited to the above embodiments andvarious changes and modifications can be made within the spirit andscope of the present invention. Therefore, to apprise the public of thescope of the present invention, the following claims are made.

1. An imaging apparatus which has a movable element related to imagingand an image sensing element, and has a function of sensing an image ofan object with the image sensing element and reading as an image signala signal generated by the image sensing element, comprising: a controlunit arranged to stop movement of the element related to imaging, and,after stopping the movement elapse of predetermined time from stoppingmovement control for the element, starting to start reading of a signalgenerated by the image sensing element.
 2. The apparatus according toclaim 1, wherein the element related to imaging is a grid arrangedbetween the object and the image sensing element.
 3. The apparatusaccording to claim 1, wherein said apparatus further comprises anirradiation detection unit arranged to detect irradiation for theobject, and said control unit controls the stopping of movement of theelement related to imaging on the basis of a detection result from saidirradiation detection unit.
 4. The apparatus according to claim 1,wherein after stopping movement of a grid, said control unit startsreading the signal from the image sensing element after an elapse of apredetermined time.
 5. The apparatus according to claim 4 1, whereinsaid control unit determines in advance the predetermined time on thebasis of at least one of an irradiation time for the object and a movingspeed of the element related to imaging.
 6. The apparatus according toclaim 1, wherein said apparatus further comprises a vibration detectionunit arranged to detect a vibration state of the image sensing elementdue to movement of the element related to imaging, and said control unitcontrols a start of reading an accumulated signal from the image sensingelement on the basis of a detection result from said vibration detectionunit.
 7. The apparatus according to claim 1, wherein irradiation for theobject includes radiation irradiation.
 8. An imaging apparatus which hasa movable element related to imaging and an image sensing element, andhas a function of sensing an image of an object with the image sensingelement and reading as an image signal a signal generated by the imagesensing element, comprising: drive unit arranged to move the elementrelated to imaging by the image sensing element; and control unitarranged to control said drive unit to operate the element related toimaging at a predetermined speed without any acceleration during anoperation period related to reading a signal from the image sensingelement.
 9. The apparatus according to claim 8, wherein the elementrelated to imaging is a grid inserted between the object and the imagesensing element.
 10. The apparatus according to claim 8, whereinirradiation for the object includes radiation irradiation.
 11. Theapparatus according to claim 10, wherein the radiation comprises X-rays.12. An imaging apparatus which has a movable element related to imagingand an image sensing element, and has a function of sensing an image ofan object with the image sensing element and reading as an image signala signal generated by the image sensing element, comprising: drive unitarranged to move the element related to imaging; and control unitarranged to control said drive unit to operate the element related toimaging at a uniform acceleration during an operation period related toreading a signal from the image sensing element.
 13. The apparatusaccording to claim 12, wherein the element related to imaging is a gridinserted between the object and the image sensing element.
 14. Theapparatus according to claim 12, wherein irradiation for the objectincludes radiation irradiation.
 15. The apparatus according to claim 14,wherein the radiation comprises X-rays.
 16. An imaging apparatus whichhas a movable element related to imaging and an image sensing element,and has a function of sensing an image of an object with the imagesensing element and reading as an image signal a signal generated by theimage sensing element, comprising: drive unit arranged to move theelement related to imaging; and control unit arranged to controlexecution of a drive operation related to image acquisition upondetermining that a value of a vibration is not more than a predeterminedvalue during an operation period related to an image read from the imagesensing element.
 17. The apparatus according to claim 16, wherein theelement related to imaging is a grid inserted between the object and theimage sensing element.
 18. The apparatus according to claim 16, whereinirradiation for the object includes radiation irradiation.
 19. Theapparatus according to claim 18, wherein the radiation comprises X-rays.20. An imaging apparatus having a function of sensing an image of anobject with an image sensing element and reading as an image signal asignal generated by the image sensing element, comprising: a drive unitarranged to move the image sensing element; and a control unit arrangedto stop movement of the image sensing element by said drive unit, and,after stopping the movement elapse of a predetermined time from stoppingmovement control for the element, starting to start reading of anaccumulated signal from the image sensing element.
 21. The apparatusaccording to claim 20, wherein after stopping movement of the imagesensing element, said control unit starts reading the signal from theimage sensing element after an elapse of a predetermined time.
 22. Theapparatus according to claim 20, wherein said apparatus furthercomprises vibration detection unit arranged to detect a vibration stateof the image sensing element, and said control unit controls a start ofreading of the signal from the image sensing element on the basis of adetection result from said vibration detection unit.
 23. The apparatusaccording to claim 20, wherein irradiation for the object includesradiation irradiation.
 24. An imaging apparatus having a function ofsensing an image of an object with an image sensing element and readingas an image signal a signal generated by the image sensing element,comprising: drive unit arranged to move the image sensing element; andcontrol unit arranged to control said drive unit to operate the imagesensing element at a predetermined speed without any acceleration duringan operation period related to reading a signal from the image sensingelement.
 25. The apparatus according to claim 24, wherein irradiationfor the object includes radiation irradiation.
 26. The apparatusaccording to claim 25, wherein the radiation comprises X-rays.
 27. Animaging apparatus having a function of sensing an image of an objectwith an image sensing element and reading as an image signal a signalgenerated by the image sensing element, comprising: drive unit arrangedto move the image sensing element; and control unit arranged to controlsaid drive unit to operate the image sensing element at a uniformacceleration during an operation period related to reading a signal fromthe image sensing element.
 28. The apparatus according to claim 27,wherein irradiation for the object includes radiation irradiation. 29.The apparatus according to claim 28, wherein the radiation comprisesX-rays.
 30. An imaging apparatus having a function of sensing an imageof an object with an image sensing element and reading as an imagesignal a signal generated by the image sensing element, comprising:drive unit arranged to move the image sensing element; and control unitarranged to control execution of a drive operation related to imageacquisition upon determining that a value of a vibration is not morethan a predetermined value during an operation period related to animage read from the image sensing element.
 31. The apparatus accordingto claim 30, wherein irradiation for the object includes radiationirradiation.
 32. The apparatus according to claim 31, wherein theradiation comprises X-rays.
 33. An imaging method of sensing an image ofan object with an image sensing element and reading a signal generatedby the image sensing element while moving a movable element related toimaging, comprising: stopping movement of the element related toimaging, and, after stopping the movement elapse of a predetermined timefrom stopping movement control for the element, starting reading of asignal from the image sensing element.
 34. An imaging method of sensingan image of an object with an image sensing element and reading a signalgenerated by the image sensing element while moving a movable elementrelated to imaging, comprising: in moving the element related to imagingat the time of image sensing by the image sensing element, controllingoperation of the element related to imaging at a predetermined speedwithout any acceleration during an operation period related to readingof a signal from the image sensing element.
 35. An imaging method ofsensing an image of an object with an image sensing element and readinga signal generated by the image sensing element while moving a movableelement related to imaging, comprising: in moving the element related toimaging at the time of image sensing by the image sensing element,controlling operation of the element related to imaging at a uniformacceleration during an operation period related to reading a signal fromthe image sensing element.
 36. An imaging method of sensing an image ofan object with an image sensing element and reading a signal generatedby the image sensing element while moving a movable element related toimaging, comprising: in moving the element related to imaging at thetime of image sensing by the image sensing element, controllingexecution of a drive related to image acquisition upon determining thata value of a vibration of the image sensing element is not more than apredetermined value during an operation period related to an image readfrom the image sensing element.
 37. An imaging method of sensing animage of an object with a movable image sensing element and reading asignal generated by the image sensing element, comprising: stoppingmovement of the image sensing element, and, after stopping the movementelapse of a predetermined time from stopping movement control for theelement, starting reading of a signal from the image sensing element.38. An imaging method of sensing an image of an object with a movableimage sensing element and reading a signal generated by the imagesensing element, comprising: controlling operation of the image sensingelement at a predetermined speed without any acceleration during anoperation period related to reading a signal from the image sensingelement.
 39. An imaging method of sensing an image of an object with amovable image sensing element and reading a signal generated by theimage sensing element, comprising: controlling operation of the imagesensing element at a uniform acceleration during an operation periodrelated to reading a signal from the image sensing element.
 40. Animaging method of sensing an image of an object with a movable imagesensing element and reading a signal generated by the image sensingelement, comprising: controlling execution of a drive operation relatedto image acquisition upon determining that a value of a vibration of theimage sensing element is not more than a predetermined value during anoperation period related to an image read from the image sensingelement.
 41. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim
 33. 42. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim
 34. 43. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim
 35. 44. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim
 36. 45. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim
 37. 46. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim
 38. 47. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim
 39. 48. A computer-readable storage medium wherein said storagemedium stores a processing program for executing said imaging method ofclaim 40.